Implantable tendon protection systems and related kits and methods

ABSTRACT

An implantable tendon protection system includes a body adapted to be implanted within a bursa overlying a tendon of a patient to protect the tendon. The body may be fixed to the tendon with adhesive, sutures, staples, and/or anchors. A surgical kit is provided with such a tendon protection system and an insertion cannula. Methods of protecting a tendon of a patient are also disclosed.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No. 14/798,921, filed on Jul. 14, 2015, which is a continuation of U.S. application Ser. No. 13/763,414, filed on Feb. 8, 2013, which is a continuation of U.S. application Ser. No. 12/684,774, filed on Jan. 8, 2010, which claims the benefit of U.S. Provisional Application No. 61/253,800, filed on Oct. 21, 2009; 61/184,198 filed on Jun. 4, 2009; 61/162,234 filed Mar. 20, 2009; 61/153,592 filed on Feb. 18, 2009, and 61/143,267 filed on Jan. 8, 2009, the disclosures of each incorporated herein by reference.

FIELD

The present invention relates generally to orthopedic medicine and surgery. More particularly, the present invention relates to methods and apparatus for delivery and fixation of sheet-like implants, such as for treating articulating joints.

BACKGROUND

Injuries to soft tissue, including, for example, musculoskeletal tissue, may require repair by surgical intervention, depending upon factors such as the severity and type of injury. Such surgical repairs can be effected by using a number of conventional surgical procedures, for example, by suturing the damaged tissue, and/or by mounting an implant to the damaged tissue. It is known that an implant may provide structural support to the damaged tissue, and it may also serve as a substrate upon which cells can grow, thus facilitating more rapid healing.

One example of a fairly common soft tissue injury is damage to the rotator cuff or rotator cuff tendons. The rotator cuff facilitates circular motion of the humerus relative to the scapula. Damage to the rotator cuff is a potentially serious medical condition that may occur during hyperextension, from an acute traumatic tear or from overuse of the joint. The most common injury associated with the rotator cuff region is a strain or tear involving the supraspinatus tendon. A tear at the insertion site of the tendon with the humerus, may result in the detachment of the tendon from the bone. This detachment may be partial or full, depending upon the severity of the injury. Additionally, the strain or tear can occur within the tendon itself. Treatment for a strained tendon usually involves physical cessation from use of the tendon, i.e., rest. However, depending upon the severity of the injury, a torn tendon might require surgical intervention as in the case of a full tear or detachment of the supraspinatus tendon from the humerus. Such surgical interventions include debridement, acromioplasty, and various procedures for reconnecting tendons to bone or strengthening damaged tendon to bone connections. Damage to the rotator cuff may also include degeneration. This is a common situation that arises in elderly patients. In degenerative cases there is loss of the superior portion of the rotator cuff with complete loss of the supraspinatus tendon. Similar soft tissue pathologies include tears in the Achilles' tendon, the anterior cruciate ligament and other tendons or ligaments of the knee, wrist, hand, and hip, spine, etc.

Some studies suggest that 85% of people over the age of 65 have some degree of shoulder tendon damage. Well-established procedures exist for repairing fully torn tendons, such as rotator cuff tendons, as previously mentioned. However, adequate treatments do not currently exist for partially torn tendons. There is a large need for less invasive surgical techniques and systems for effecting tendon repair, particularly for the supraspinatus tendon.

SUMMARY OF THE DISCLOSURE

In accordance with aspects of the disclosure, an implantable tendon protection system is provided which comprises a body adapted to be implanted within a bursa overlying a tendon of a patient. The body comprising a tendon engaging surface configured to attach to the tendon. The body may further comprise a sliding surface adapted to slide with respect to the bursa. In some embodiments, the tendon engaging surface comprises adhesive. The body may be configured to be movable between a collapsed state in which the body may be received within a cannula cavity, and a deployed state in which the body may extend across an interior portion of the bursa. In some embodiments, the body is configured to attach to a partially torn tendon. The body may comprise a middle portion that is less flexible than an edge portion.

In some of the above embodiments, the body is constructed from individual layers. A first layer may comprise a sliding surface and a second layer may comprise a tendon engaging surface, a mesh material, a plurality of fibers, and/or a bioabsorbable material. One or more intermediate layers may be located at least partially between the first and second layers. In some embodiments, a cushioning layer is interposed between the first and second layers. An intermediate layer may comprise at least one channel which may fluidly communicate with the tendon engaging surface. In some embodiments the sliding surface has a lower coefficient of friction than that of the tendon engaging surface.

In accordance with other aspects of the disclosure, a surgical kit is provided which comprises a system such as described above and an insertion cannula. The insertion cannula may include a portion configured to enter a body of a patient. This portion includes a cavity for receiving the system when in a collapsed state. The insertion cannula may further comprise a mechanism configured to remove the system from the cavity when the insertion cannula portion is within the body of the patient. The removal mechanism may comprise a push rod at least partially located within the insertion cannula and movable along a longitudinal axis of the insertion cannula.

In accordance with other aspects of the disclosure, methods of protecting a tendon of a patient are disclosed. In some embodiments, the method includes the steps of inserting a device into an at least partially viable bursa of the patient to a position overlying the tendon, and engaging a first surface of the implant with the tendon. The method may further include the step of attaching the device to the tendon. In some embodiments, the attaching step comprises the use of an adhesive. The adhesive may be urged through a channel in the device when the device is positioned within the body of the patient. In some embodiments, the inserting step comprises at least partially receiving the device within a portion of an insertion instrument, inserting the portion of the insertion instrument into the body of the patient, and removing the device from the insertion instrument while the portion is within the body. The device may be caused to assume the deployed state at least partially by introducing a fluid into an inflatable portion of the device.

In some embodiments, the above methods may further comprise the step of delivering a therapeutic or diagnostic agent to tissue adjacent the device. The therapeutic or diagnostic agent may include a drug, anti-inflammatory agent, painkiller, antibiotic, protein, and/or a hormone.

In some embodiments, a second surface of the device is deployed to slide relative to the bursa. The device may serve to protect a damaged portion of the tendons. In some embodiments, the device does not substantially reinforce the engaged tendons by transmitting a significant load of the tendons. The device may serve to remove a stimulus from nerves in the engaged tendons. The removed stimulus may include one or more of pressure, temperature, chemical, electrical and inflammation stimulus. In some embodiments the device is not sutured to the tendons or other tissue. The inserting step may comprise the use of an arthroscopic instrument. In some embodiments the tendon comprises a partially torn tendon. The attaching step may comprise securing the device to the tendon using a plurality of anchors.

In accordance with other aspects of the disclosure, a method is provided which comprises identifying a partially torn portion of a tendon and covering the partially torn portion of the tendon. In some embodiments a device may be positioned over the partially torn portion of the tendon and fixed to the tendon. The device may be fixed to the tendon with adhesive, sutures, staples, and/or anchors. Covering the partially torn portion of the tendon may spread impinging forces across a surface area of the device. In some embodiments a therapeutic agent that promotes growth of tissue into pores defined by the device may be delivered. The therapeutic agent may promote encapsulation of the device within a cellular encapsulation layer. The therapeutic agent may induce the growth of synovial cells on an outer surface of the device. The therapeutic agent may induce the growth of bursa cells on an outer surface of the device. The therapeutic agent may desensitize stimulated nerve receptors proximate the partially torn portion of the tendon. The therapeutic agent may promote the growth of a cellular encapsulation barrier over the partially torn portion of the tendon.

In some embodiments, covering the partially torn portion of the tendon inhibits the partially torn portion of the tendon from becoming a tear extending through a total thickness of the tendon. Covering the partially torn portion of the tendon may inhibit physical stimulus of the partially torn portion by adjacent tissues. Covering the partially torn portion of the tendon may protect damaged tendon fibers from mechanical agitation by adjoining tissues. Covering the partially torn portion of the tendon may alleviate pain, which in turn may restore shoulder function. In some embodiments, covering the partially torn portion of the tendon protects the partially torn portion of the tendon. Covering the partially torn portion of the tendon may prevent abrasion of the partially torn portion of the tendon. Covering the partially torn portion of the tendon may reduce friction between the partially torn portion of the tendon and adjacent tissues. Covering the partially torn portion of the tendon may cushion forces applied to the partially torn portion of the tendon by adjacent tissues.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is an anterior view showing the upper torso of a patient with the left shoulder shown in cross-section.

FIG. 2 is an enlarged, cross-sectional view showing the left shoulder depicted in FIG. 1.

FIG. 3 is an enlarged, cross-sectional view showing an exemplary implantable device in accordance with aspects of the invention inserted into the shoulder.

FIG. 4 is an enlarged, oblique, cross-sectional view showing an exemplary cannula inserted into the bursa of the shoulder.

FIG. 5 is an enlarged, oblique, cross-sectional view showing an exemplary delivery system inserted into the shoulder.

FIG. 6 shows the delivery system of FIG. 5 with the sheath retracted.

FIG. 7 shows the delivery system of FIG. 5 with the implantable device completely deployed.

FIG. 8 shows the implantable device in place with the delivery system of FIG. 5 removed.

FIG. 9 is an exploded isometric view illustrating an exemplary implantable device.

FIG. 10 is a stylized block diagram illustrating an exemplary implantable device coupled to a syringe.

FIGS. 11A, 11B, and 11C are a series of isometric views illustrating the deployment of an exemplary implantable device.

FIG. 12 is a plan view illustrating an exemplary implantable device.

FIG. 13 is a side cross-sectional view taken along line A-A in FIG. 12.

FIG. 14 is a side cross-sectional view taken along line A-A in FIG. 12 and illustrating the device of FIG. 12 anchored to a tendon.

DETAILED DESCRIPTION

The following detailed description should be read with reference to the drawings in which similar elements in different drawings are numbered the same. The drawings, which are not necessarily to scale, depict illustrative embodiments and are not intended to limit the scope of the invention.

FIG. 1 is a stylized anterior view of a patient 28. For purposes of illustration, a shoulder 26 of patient 28 is shown in cross-section in FIG. 1. Shoulder 26 includes a humerus 24 and a scapula 23. The movement of humerus 24 relative to scapula 23 is controlled by a number of muscles including: the deltoid, the supraspinatus, the infraspinatus, the subscapularis, and the teres minor. For purposes of illustration, only the supraspinatus 30 is shown in FIG. 1. With reference to FIG. 1, it will be appreciated that a distal tendon 22 of the supraspinatus 30 meets humerus 24 at an insertion point 32.

FIG. 2 is an enlarged cross sectional view of shoulder 26 shown in the previous figure. In FIG. 2, a head 36 of humerus 24 is shown mating with a glenoid fossa of scapula 23 at a glenohumeral joint 38. The glenoid fossa comprises a shallow depression in scapula 23. A supraspinatus 30 and a deltoid 34 are also shown in FIG. 2. These muscles (along with others) control the movement of humerus 24 relative to scapula 23.

A distal tendon 22 of supraspinatus 30 meets humerus 24 at an insertion point 32. In the embodiment of FIG. 2, tendon 22 includes a damaged portion 140 located near insertion point 32. Damaged portion 140 includes a tear 142 extending partially through tendon 22. Tear 142 may be referred to as a partial thickness tear. Tendon 22 of FIG. 2 has become frayed. A number of loose tendon fibers 144 are visible in FIG. 2.

Scapula 23 includes an acromium 21. In FIG. 2, a subacromial bursa 20 is shown extending between acromium 21 of scapula 23 and head 36 of humerus 24. In FIG. 2, subacromial bursa 20 is shown overlaying supraspinatus 30. Subacromial bursa 20 is one of more than 150 bursae found the human body. Each bursa comprises a fluid filled sac. The presence of these bursae in the body reduces friction between bodily tissues. Injury and/or infection of the bursa can cause it to become inflamed. This condition is sometimes referred to as bursitis.

FIG. 3 is an additional cross sectional view of shoulder 26 shown in the previous figure. In the embodiment of FIG. 3, a device 4 has been implanted inside subacromial bursa 20. Device 4 comprises a body 150. Body 150 is adapted to be implanted within a bursa overlying a tendon of a patient.

In FIG. 3, body 150 of device 4 is shown overlaying tear 142. In the exemplary embodiment of FIG. 3, body 150 comprises a first side 152 and a second side 154. First side 152 comprises a sliding surface 156 and second side 154 comprises a tendon engaging surface 158. Sliding surface 156 is adapted to slide with respect to adjacent tissues (e.g., bursa tissue). Tendon engaging surface 158 is configured to attach to a tendon.

In the exemplary embodiment of FIG. 3, fibers 144 of tendon 22 are fixed to device 4 by an adhesive 160. Adhesive 160 is illustrated using dots in FIG. 3. With reference to FIG. 3, it will be appreciated that adhesive 160 permeates a portion of device 4. Some exemplary methods in accordance with the present detailed description include injecting an adhesive into channels defined by a device so that the adhesive exits a plurality of apertures defined by a tissue engaging layer of the device. The adhesive may elute over a large area to affix the device to a tendon. Some additional exemplary methods in accordance with the present detailed description include injecting a therapeutic agent (e.g., a drug) into channels defined by a device so that the therapeutic agent exits a plurality of apertures defined by a tissue engaging layer of the device.

FIG. 4 is an isometric view of a shoulder 26. Shoulder 26 includes a humerus 24 and a scapula 23. Humerus 24 comprises a head 36 having a generally spherical surface. Head 36 of humerus 24 mates with a shallow depression defined by the scapula 23 at a glenohumeral joint 38. In FIG. 4, a distal tendon 22 of a supraspinatus 30 is shown meeting humerus 24 at an insertion point. Supraspinatus 30 (along with a number of other muscles) controls the movement of humerus 24 relative to scapula 23.

In FIG. 4, a subacromial bursa 20 is shown overlaying a portion of supraspinatus 30. Subacromial bursa 20 comprises a fluid filled sac that acts to reduce friction between tissues in the body. In FIG. 4, subacromial bursa 20 is shown extending between a portion of supraspinatus 30 and an acromium 21 of scapula 23. In the embodiment of FIG. 4, the distal end of a cannula 162 has been inserted into the interior of bursa 20. Cannula 162 may be inserted, for example, near a site where tendon damage exists. Cannula 162 includes a shaft 164 defining a lumen and a hub 166 that is fixed to a proximal end of shaft 164. In the embodiment of FIG. 4, the lumen defined by cannula 162 fluidly communicates with an interior of subacromial bursa 20. Accordingly, a device may be placed in the interior of subacromial bursa 20 by advancing that device through the lumen defined by cannula 162.

FIG. 5 is an additional isometric view of shoulder 26 shown in the previous figure. A delivery system 170 is shown in FIG. 5. Delivery system 170 of FIG. 5 comprises a sheath 3, a barrel 2, and a plunger 1. In the embodiment of FIG. 5, a device 4 is disposed inside sheath 3. Some methods in accordance with the present detailed description may include the step of causing the body of a device to assume a collapsed shape and inserting the body of the device into a sheath. The sheath and the body of the device may both be inserted into a bursa. Once inside the bursa, the body may assume a deployed shape.

It is to be appreciated that the length of delivery system 170 may vary from that shown in FIG. 5 without deviating from the spirit and scope of the present detailed description. In useful some embodiments, a portion of delivery system 170 may extend through a cannula (e.g., the cannula shown in the previous figure). The cannula may guide the distal end of delivery system 170 to a target site.

FIG. 6 is an additional isometric view showing delivery system 170 shown in the previous figure. In the embodiment of FIG. 6, sheath 3 of delivery system 170 has been retracted from device 4, exposing device 4. In other embodiments, sheath 3 may remain stationary while device 4 is extended from within the sheath, or device 4 may be deployed with a combination of movements of the sheath and the device. In some useful embodiments, device 4 assumes a generally cylindrical shape while disposed inside sheath 3. In the embodiment of FIG. 6, deployment of device 4 has been initiated. Accordingly, device 4 is shown assuming a somewhat enlarged shape in FIG. 6.

FIG. 7 is an additional isometric view showing delivery system 170 shown in the previous figure. In FIG. 7, device 4 is shown assuming a completely deployed shape. In the exemplary embodiment of FIG. 7, device 4 is generally plate-shaped and circular when fully deployed. In some advantageous embodiments, the body of device 4 is flexible.

Some exemplary methods in accordance with the present detailed description include injecting an adhesive into channels defined by a device so that the adhesive exits a plurality of apertures defined by a tissue engaging layer of the device. The adhesive may elute over a large area to affix the device to a tendon. Delivery system 170 may be withdrawn from shoulder 26 after the delivery of device 4 is complete.

FIG. 8 is an additional cross sectional view of shoulder 26 shown in the previous figure. In the embodiment of FIG. 8, device 4 has been implanted inside subacromial bursa 20. In FIG. 8, device 4 is shown overlaying a portion of distal tendon 22 of supraspinatus 30. In the exemplary embodiment of FIG. 8, device 4 comprises a body 150 having a first side 152 and a second side 154. First side 152 comprises a sliding surface 156 and second side 154 comprises a tendon engaging surface 158. In the embodiment of FIG. 8, body 150 has been positioned so that tendon engaging surface 158 engages tendon 22. Tendon engaging surface 158 may be fixed to distal tendon 22, for example, with an adhesive. When device 4 is overlaying tendon 22 as shown in FIG. 8, device 4 provides a sliding surface 156 facing away from tendon 22.

FIG. 9 is an exploded isometric view illustrating an exemplary device 304 in accordance with the present detailed description. In the exemplary embodiment of FIG. 9, device 304 comprises a body 350 including a first layer 372, a second layer 374, a first intermediate layer 376, and a second intermediate layer 378.

When device 304 is overlaying tendon 22, first layer 372 of device 304 provides a sliding surface 356 facing away from the tendon. In the exemplary embodiment of FIG. 9, second layer 374 comprises a biocompatible material for use against the tendon surface. In the embodiment of FIG. 9, second layer 374 defines a plurality of apertures 380. In one exemplary embodiment, second layer 374 comprises a mesh material. In some embodiments, second layer 374 may comprise a plurality of fibers. The fibers may be interlinked with one another. When this is the case, second layer 374 may comprise a plurality of apertures comprising the interstitial spaces between fibers. Various processes may be used to interlink the fibers with one another. Examples of processes that may be suitable in some applications including weaving, knitting, and braiding.

In some useful embodiments, second layer 374 comprises one or more bioabsorbable materials. Examples of bioabsorbable materials that may be suitable in some applications include those in the following list, which is not exhaustive: polylactide, poly-L-lactide (PLLA), poly-D-lactide (PDLA), polyglycolide (PGA), polydioxanone, polycaprolactone, polygluconate, polylactic acid-polyethylene oxide copolymers, modified cellulose, collagen, poly(hydroxybutyrate), polyanhydride, polyphosphoester; poly(amino acids), poly(alpha-hydroxy acid) or related copolymers materials.

In the exemplary embodiment of FIG. 9, second intermediate layer 378 comprises a plate defining a plurality of channels. Channels 382 of second intermediate layer 378 and apertures 380 of second layer 374 may allow a fluid to elute over a large area to device 304 to a tendon. Second intermediate layer 378 may also distribute stresses across device 304. When pressure from adjacent tissues is applied to device 304, the device will spread that pressure across an area of a tendon covered by device 304. This function helps device 304 to reduce stimulus to nerves in the covered tendon.

A second inlet 386 is visible in FIG. 9. An interior of second inlet 386 is in fluid communication with channels 382 of second intermediate layer 378. When device 304 is in an assembled state, channels 382 fluidly communicate with apertures 380 defined by second layer 374. Fluid may be injecting into channels 382 and through apertures 380 by injecting the fluid into second inlet 386. In one method in accordance with the present detailed description, an adhesive fluid is injected into channels 382. The adhesive fluid may elute over a tissue engaging area of device 304 to affix device 304 to a tendon.

In the exemplary embodiment of FIG. 9, first intermediate layer 376 comprises a plurality of sheets defining a cavity 388. Various fluids may be injected into cavity 388. Some exemplary methods in accordance with the present detailed description may include changing the shape of shape of device 304. The shape of device 304 may be changed, for example, by injecting fluid into cavity 388. A first inlet 384 is shown in FIG. 9. An interior of first inlet 384 is in fluid communication with cavity 388 of first intermediate layer 376. Fluid may be injected into cavity 388 by injecting the fluid into first inlet 384.

FIG. 10 is a stylized block diagram illustrating an exemplary device 504 in accordance with the present detailed description. In the exemplary embodiment of FIG. 10, device 504 comprises a body 550 including a first layer 572, a second layer 574, a first intermediate layer 576, and a second intermediate layer 578.

In the embodiment of FIG. 10, second intermediate layer 578 comprises a plurality of flow channels. A tube 590 defines a lumen that is in fluid communication with the flow channels of intermediate layer. In the embodiment of FIG. 10, a proximal end of tube 590 is coupled to a syringe 592. Syringe 592 comprising a barrel 2 and a plunger 5. A fluid 594 is disposed in barrel 2. Plunger 5 of syringe 592 is capable of urging fluid 594 out of barrel 2, through tube 590, through second intermediate layer 578, and through second layer 574. The flow of fluid 594 through second intermediate layer 578 and second layer 574 is illustrated using a plurality of arrows in FIG. 10. Fluid 594 may be urged through a plurality of apertures defined by second layer 574. Fluid 594 that has exited second layer 574 is represented by a number of fluid drops in the stylized block diagram of FIG. 10.

Some exemplary methods in accordance with the present detailed description may include the step of delivering a therapeutic or diagnostic agent to tissue adjacent a device such as, for example, device 504 of FIG. 10. The fluid may comprise various therapeutic or diagnostic agents. Examples of therapeutic or diagnostic agents that may be suitable in some applications include drugs, anti-inflammatory agents, painkillers, antibiotics, proteins, and hormones.

FIGS. 11A, 11B, and 11C are a series of isometric views illustrating the deployment of a device 4. Some methods in accordance with the present detailed description may include the step of causing the body of a device to assume a collapsed shape and inserting the body of the device into a sheath. The sheath and the body of the device may both be inserted into a bursa. Once the body is inside the bursa, the body may be urged to assume a deployed shape and/or self-deploy.

In the embodiment of FIG. 11A, device 4 is disposed inside a sheath 3 of a delivery system 170. The body of device 4 may be wrapped at least partially around itself to assume a generally collapsed shape. In some useful embodiments, the body of device 4 is capable of assuming a generally cylindrical collapsed shape while disposed inside a lumen of sheath 3. The body of device 4 may also be folded to assume a generally collapsed shape.

In the embodiment of FIG. 11B, sheath 3 has been retracted from device 4. Device 4 can be seen disposed outside of sheath 3 in FIG. 11B. In the embodiment of FIG. 11B, deployment of device 4 has been initiated. Accordingly, device 4 is shown assuming a somewhat enlarged shape in FIG. 11B.

In the embodiment of FIG. 11C, device 4 has been fully deployed. In the exemplary embodiment of FIG. 11, device 4 is generally plate shaped when fully deployed. In FIG. 4, the outer edge of device 4 is shown having a generally circular shape. In the exemplary embodiment of FIG. 11, device 4 comprises a body 150 having a first side 152 and a second side 154. First side 152 comprises a sliding surface 156 and second side 154 comprises a tendon engaging surface 158. In some useful methods, device 4 is oriented over a tendon so that tendon engaging surface 158 engages the tendon.

FIGS. 12 through 14 show an additional device 700 in accordance with the present detailed description. Device 700 may be used, for example, to cover an injured portion of a tendon. FIG. 12 is a top view of device 700. FIG. 13 is section view of device 700 taken along section line A-A shown in FIG. 12. FIG. 14 is a section view similar to FIG. 13 showing device 700 in place over tendon 736.

As best seen in FIG. 13, exemplary device 700 comprises a base 702 having a first major side 704 and a second major side 706 that is opposite first major side 704. In this embodiment, first major side 704 comprises a generally concave surface 720 and second major side 706 comprises a generally convex surface 722. A sheet 724 of device 700 may be provided to overlay first major side 704 of base 702 and generally conforms to the shape of concave surface 720.

As shown in FIG. 13, sheet 724 of device 700 defines a cavity 726. In some useful embodiments, cavity 726 is dimensioned to receive a portion of a suprapinatus tendon overlying the head of a humerus. In the exemplary embodiment of FIG. 13, cavity 726 has a generally hemispherical shape. It will be appreciated that the radius of cavity 726 may vary across cavity 726 without deviating from the spirit and scope of the present description. With reference to the figures, it will be appreciated that a skirt portion 728 of sheet 724 extends beyond base 702 in this embodiment.

In some useful embodiments, sheet 724 comprises a material defining a plurality of pores that encourage tissue growth therein. A coating that encourages tissue growth or ingrowth may be applied to the surfaces of sheet 724. It will be appreciated that sheet 724 may comprise various pore defining structures without deviating from the spirit and scope of the present description. In some embodiments, the sheet 724 has a pore size in the range of 150 to 200 microns. The porosity may be about 50 percent. Examples of pore defining structures that may be suitable in some applications include open cell foam structures, mesh structures, and structures comprising a plurality of fibers. In some embodiments, the fibers may be interlinked with one another. Various processes may be used to interlink the fibers with one another. Examples of processes that may be suitable in some applications include weaving, knitting, and braiding.

Device 700 includes a plurality of anchors 730. In the exemplary embodiment shown, each anchor comprises a coil 732. It will be appreciated that anchors 730 may comprise other elements without deviating from the spirit and scope of the present description. Examples of anchoring elements that may be suitable in some applications include: coils, barbs, hooks, stables, suture pads, and sutures. In the embodiment of FIG. 13, each anchor is disposed in a lumen 734 defined by base 702. Some methods in accordance with the present description may include the step of rotating anchors 730 to screw the anchors into tissue (e.g., tendon tissue) for fixing device 700 to that tissue. A flexible catheter or other suitable driver may used to rotate anchors 730. For example, a catheter (not shown) may be removably inserted into each of the lumens 734 in turn, accessing each lumen through a central recess 735 located in second major side 706 of base 702. In some embodiments, anchors 730 threadably engage with interior surfaces of lumens 734 to facilitate advancement of the anchor into tissue.

In FIG. 14, device 700 is shown overlaying a tendon 736. To place device 700 over tendon 736, device 700 may be configured to be collapsible so that it may be inserted into the body arthroscopically, similar to the previously described devices. For example, device 700 may be collapsed like an umbrella, with its lumens 734 being substantially parallel and the material between lumens 734 forming inwardly folding pleats when in the collapsed state.

In the embodiment of FIG. 14, each coil 732 is shown extending out of a lumen 734 and into tendon 736. Tendon 736 may be, for example, a supraspinatus tendon. With reference to FIG. 14, it will be appreciated that the diameter of each coil 732 has become enlarged as it exits a lumen 734. In some useful embodiments, each coil 732 is biased to assume an increased diameter as it exits a lumen 734. In FIG. 14, each coil 732 is shown extending through a skirt portion 728 of sheet 724 that extends beyond base 702, and then into tendon 736 to secure or assist in securing device 700 to the tendon. In this embodiment, the middle and edge portions are configured to help distract a humeral head in abduction.

In other embodiments (not shown), a device may be provided with lumens having a steeper or shallower angle relative to tendon 736. While the exemplary device 700 shown in FIGS. 12-14 employs six anchors, other devices constructed in accordance with aspects of the present description may be provided with a smaller or larger number of anchors. In other embodiments, sutures, staples, adhesive and/or other fasteners may be used in conjunction with or instead of anchors 730 to secure device 700 to the underlying tissue. Preformed holes may also be provided in sheet 724 to allow anchors 730 to pass through. In other embodiments, sheet 724 may be omitted. In still other embodiments, the device may have more or less of a cup shape, be generally flat, or inverted such that the anchors emerge from the convex side rather than the concave side. The device may be oblong, curved in only one dimension, or be saddle-shaped, depending on the particular anatomy it is designed to protect.

An implantable device such as previously described may be placed over a partial tear in a tendon. In some embodiments, the device may be implanted over a tendon having micro-tear(s), abrasions and/or inflammation. Left untreated, minor or partial tendon tears may progress into larger or full tears. According to aspects of the present invention, a small or partial tear may be treated by protecting it with an implantable device as described above. Such early treatment can promote healing and prevent more extensive damage from occurring to the tendon, thereby averting the need for a more involved surgical procedure.

The implanted device may serve to protect a tendon from a stimulus. The stimulus may comprise one or more of the following: pressure, friction, temperature, electrical or chemical stimulus. In some embodiments, the device does not supplant or share any substantial load borne by a tendon, but serves to protect the tendon to facilitate healing.

In some embodiments, a bursa overlying a tendon is left substantially intact as the device is implanted over the tendon. This may be accomplished by creating a small incision or puncture through one wall of the bursa through which the device delivery cannula may be placed. The bursa may be filled with saline or similar fluid during the procedure to keep it inflated, thereby providing sufficient operating space for deploying and attaching the implantable device. After the device is implanted and the delivery cannula is removed, the opening in the bursa may be closed, such as with one or more sutures. Alternatively, it is believed that the bursa may form closure tissue by itself post-operatively. Such bursa growth may be stimulated by movement of the tendon and/or bursa relative to surrounding tissue.

In other embodiments, a portion or all of the bursa may be removed during the implantation procedure. In these embodiments, the implantable device may be sized and positioned to facilitate the bursa reforming naturally in its original location after the procedure.

As previously indicated, the implantable device may comprise an absorbable material. In some embodiments, the purpose of the device is to protect an injured portion of a tendon during healing, provide a scaffolding for new tissue growth, and/or temporarily share some of the tendon loads. The device may induce additional tendon tissue formation, thereby adding strength and reducing pain, micro strains and inflammation. When the device is applied to a structurally intact, partially torn tendon, the initial loading of the device may be carried by native tendon tissue until collagen is formed during the healing process. In some embodiments, organized collagen fibers are created that remodel to neo tendon with cell vitality and vascularity. Initial stiffness of the device may be less than that of the native tendon so as to not overload the fixation while tendon tissue is being generated.

The implantable device may be configured to allow loading and retention of biologic growth factors. The device and/or the growth factors may be configured to controllably release the growth factors. The device may be configured to allow transmission of body fluid to remove any degradation bi-products in conjunction with a potential elution profile of biologics. The device should degrade over time with minimal inflammatory response. For example, particulate matter that may result from degradation should not generate synovitus in the joint.

In one exemplary embodiment, the implantable device has a diameter of about 22 mm, and has directionally specific mechanical properties. In another embodiment, the device is generally rectangular with a width of about 20 mm, a length of about 40 mm, and a thickness of about 1 mm. In another embodiment, the device has a length of about 30 mm. These latter two arrangements provide a 20 mm2 cross-sectional area transverse to the load direction.

It is desirable in some situations to generate as much tissue as possible within anatomical constraints. In some cases where a tendon is degenerated or partially torn, tendon loads are relatively low during early weeks of rehabilitation. For example, the load may be about 100 N. The strain in the tendon due to the load during rehabilitation can be about 2%. In some of these cases, the implantable device can be designed to have an ultimate tensile strength of at least about 5 MPa. The tensile modulus can be designed to be no more than about 50 MPa and no less than about 20 MPa. The compressive modulus can be designed to be at least about 0.5 MPa. With a tensile modulus of 50 MPa, in order for the scaffold to strain 2% in conjunction with the degenerated tendon, the stress on the scaffold will be about 1.0 MPa. With an ultimate tensile strength of 5 MPa, the strength of the scaffolding of the implantable device when first implanted will be about five times the expected loads. With a cross-sectional area of 20 mm2, the load on the scaffold will be 20 N. Thus, from a load sharing perspective, the scaffold will carry about 20% of the load to experience 2% strain.

A published value for the compressive modulus of the supraspinatus tendon is in the range of 0.02-0.09 MPa (J Biomech Eng 2001, 123:47-51). The scaffold provided by the implantable device should have a higher compressive modulus than the tendon to prevent collapse of pores in the scaffold. A compressive modulus of 0.5 MPa would be about five times greater than the tendon.

The tissue within the device scaffold will typically be developing and organizing during the first one to three months after implantation, so load sharing with the scaffold is desired in some embodiments. After three months the tissue will typically be remodeling, so the mechanical properties of the scaffold should gradually decline to zero to enable the new tissue to be subjected to load without the scaffold bearing any of the load. If the scaffold loses modulus faster than it loses strength, then the relative loads on the scaffold will be less at three months than when first implanted. For example, if the modulus of the scaffold drops 50% to 25 MPa at three months, then 2% strain of the scaffold would require a stress of only about 0.5 MPa. At the same time, if the strength of the scaffold drops about 30% to 3.5 MPa, then the strength of the scaffold will be about seven times the anticipated loads at three months, compared to about five times when first implanted. Therefore, with the design criteria provided above, tensile failure of the scaffold during the first three months should be unlikely. Accordingly, the following specifications for degradation rate are recommended in some embodiments: an ultimate tensile strength of at least 70% strength retention at three months; tensile and compressive modulus of at least 50% strength retention at three months; and no minimum specification for strength and modulus at 6 months. The device may be designed to have a degradation profile such that it is at least 85% degraded in less than 1 to 2 years after implantation.

Cyclic creep is another design constraint to be considered in some embodiments. A strain of about 2% with a 40 mm long scaffold will result in an elongation of about only 0.8 mm. Therefore, very little cyclic creep can be tolerated in these embodiments to ensure that the scaffold will undergo strain with each load cycle. A test where a proposed scaffold design is cyclically strained to 2% at 0.5 Hz for 1 day provides 43,200 cycles, which likely exceeds the number of cycles experienced in three months of rehabilitation of a patient's joint. Incorporation of relaxation times should be considered in such testing. In some embodiments, a maximum of about 0.5% creep is an acceptable specification.

Material(s) used in the implanted device should be able to withstand the compression and shear loads consistent with accepted post surgical shoulder motions. The perimeter of the device may have different mechanical properties than the interior of the device, such as for facilitating better retention of sutures, staples or other fastening mechanisms. The material(s) may be chosen to be compatible with visual, radiographic, magnetic, ultrasonic, or other common imaging techniques. The material(s) may be capable of absorbing and retaining growth factors with the possibility of hydrophilic coatings to promote retention of additives.

While the systems, kits and methods disclosed above have been discussed relative to protecting tendons in shoulder joints, they may also be utilized to protect tendons in other articulating joints such as the knee, elbow and ankle.

While exemplary embodiments of the present invention have been shown and described, modifications may be made, and it is therefore intended in the appended claims to cover all such changes and modifications which fall within the true spirit and scope of the invention. 

What is claimed is:
 1. A method of treating a partial thickness tear of a supraspinatus tendon in a shoulder region of a patient comprising: inserting a distal end of an implant delivery device into the shoulder region of the patient proximate a supraspinatus muscle, the implant delivery device comprising: a sheath defining a lumen; and an implant disposed within the lumen of the sheath; transitioning the implant from an undeployed state within the sheath to a deployed state outside of the sheath; positioning the implant over the partial thickness tear of the supraspinatus tendon of the patient in the deployed state; and attaching the implant to the supraspinatus tendon of the patient while the implant is positioned over the partial thickness tear of the supraspinatus tendon of the patient; wherein the implant includes a layer comprising a plurality of fibers with interstitial spaces therebetween for accommodating tissue ingrowth therein.
 2. The method of claim 1, wherein upon implantation the implant shares some of an applied load on the supraspinatus tendon; and wherein the implant induces additional tendon tissue formation over time to reduce an amount of loading sharing of the applied load on the supraspinatus tendon by the implant.
 3. The method of claim 2, wherein the amount of load sharing of the applied load on the supraspinatus tendon by the implant gradually declines to zero by three months after implantation.
 4. The method of claim 2, wherein the implant has a tensile modulus at implantation of no more than 50 MPa.
 5. The method of claim 4, wherein the implant is configured to degrade in tensile modulus over time.
 6. The method of claim 1, wherein the implant has a tensile modulus at implantation of no more than 50 MPa.
 7. The method of claim 6, wherein the implant comprises a bioabsorbable material and is configured to degrade in tensile modulus over time.
 8. The method of claim 1, further comprising attaching the implant to the supraspinatus tendon using staples.
 9. A method of implanting an implant in a shoulder region of a patient comprising: inserting a distal end of an implant delivery device into a shoulder region of the patient proximate a supraspinatus muscle, the implant delivery device comprising: a sheath defining a lumen extending to a distal end of the sheath; and an implant comprising a bioabsorbable material disposed within the lumen of the sheath; deploying the implant from the lumen of the sheath by moving the implant relative to the distal end of the sheath; positioning the implant over a partial thickness tear of a supraspinatus tendon of the patient in a deployed configuration; while the implant is positioned over the partial thickness tear of the supraspinatus tendon of the patient, attaching the implant to the supraspinatus tendon of the patient without using sutures.
 10. The method of claim 9, further comprising attaching the implant to the supraspinatus tendon using staples.
 11. The method of claim 9, wherein the implant is a multi-layer implant including a first layer and a second layer juxtaposed with the first layer, the first layer being different from the second layer, the first layer comprising a plurality of fibers with interstitial spaces therebetween for accommodating tissue ingrowth therein.
 12. The method of claim 9, wherein the implant has a tensile modulus of no more than 50 MPa at implantation.
 13. The method of claim 12, wherein the implant is configured to degrade in tensile modulus over time.
 14. A method of implanting an implant in a shoulder region of a patient comprising: inserting a distal end of an implant delivery device into a bursa of the shoulder region of the patient proximate a supraspinatus muscle, the implant delivery device comprising: a sheath defining a lumen; and a multi-layer implant disposed within the lumen of the sheath in a compact configuration, the implant including a first layer and a second layer juxtaposed with the first layer, the first layer being different from the second layer, the first layer comprising a plurality of fibers and interstitial spaces therebetween for accommodating tissue ingrowth therein; deploying the implant from the sheath within the bursa such that the implant transitions to a deployed configuration; positioning the implant over a tear of a supraspinatus tendon of the shoulder region of the patient with the first layer placed against the supraspinatus tendon; and attaching the implant to the supraspinatus tendon of the patient with the implant positioned over the tear of the supraspinatus tendon of the patient without using sutures.
 15. The method of claim 14, wherein upon attaching the implant to the supraspinatus tendon, a load on the supraspinatus tendon is transferred through the second layer of the implant while new tendon tissue is generated within the interstitial spaces of the first layer of the implant.
 16. The method of claim 15, wherein the implant has a tensile modulus of no more than 50 MPa at implantation.
 17. The method of claim 16, wherein the implant is configured to degrade in tensile modulus over time.
 18. The method of claim 17, wherein at three months after implantation, the implant retains at least 50% of its tensile modulus at implantation.
 19. The method of claim 14, wherein attaching the implant to the supraspinatus tendon includes using staples.
 20. The method of claim 14, wherein the interstitial spaces have a pore size in the range of 150 microns to 200 microns. 